Fluidics-based assay devices

ABSTRACT

A fluidics-based assay device for detecting the presence or quantity of an analyte residing in a test sample is provided. The device utilizes a self-calibrated magnetic binding assay format (e.g., sandwich, competitive, etc.) that includes detection probes capable of generating a detection signal (e.g., fluorescent non-magnetic particles) and calibration probes capable of generating a calibration signal (e.g., fluorescent magnetic particles). The amount of the analyte within the test sample is proportional (e.g., directly or inversely) to the intensity of the detection signal calibrated by the intensity of the calibration signal. It has been discovered that the fluidics-based device of the present invention provides an accurate, inexpensive, and readily controllable method of determining the presence of an analyte in a test sample.

BACKGROUND OF THE INVENTION

[0001] Various analytical procedures and devices are commonly employed in assays to determine the presence and/or absence of analytes in a test sample. For instance, immunoassays utilize mechanisms of the immune systems, wherein antibodies are produced in response to the presence of antigens that are pathogenic or foreign to the organisms. These antibodies and antigens, i.e., immunoreactants, are capable of binding with one another, thereby causing a highly specific reaction mechanism that can be used to determine the presence or concentration of that particular antigen in a biological sample.

[0002] There are several well-known immunoassay methods that use immunoreactants labeled with a detectable component so that the analyte can be detected analytically. For example, “sandwich-type” assays typically involve mixing the test sample with antibodies to the analyte. These antibodies are mobile and linked to a label or probe, such as dyed latex, a colloidal metal sol, or a radioisotope. This mixture is then contacted with a chromatographic medium containing a band or zone of immobilized antibodies to the analyte. The chromatographic medium is often in the form of a strip resembling a dipstick. When the complex of the analyte and the labeled antibody reaches the zone of the immobilized antibodies on the chromatographic medium, binding occurs and the bound labeled antibodies are localized at the zone. This indicates the presence of the analyte. This technique can be used to obtain quantitative or semi-quantitative results. Some examples of such sandwich-type assays are described by U.S. Pat. No. 4,168,146 to Grubb, et al. and U.S. Pat. No. 4,366,241 to Tom, et al.

[0003] An alternative technique is the “competitive-type” assay. In a “competitive-type” assay, the label is typically a labeled analyte or analyte-analogue that competes for binding of an antibody with any unlabeled analyte present in the sample. Competitive assays are typically used for detection of analytes such as haptens, each hapten being monovalent and capable of binding only one antibody molecule. Examples of competitive immunoassay devices are described in U.S. Pat. No. 4,235,601 to Deutsch, et al., U.S. Pat. No. 4,442,204 to Liotta, and U.S. Pat. No. 5,208,535 to Buechler, et al.

[0004] Magnetic binding assays have been widely used for separation of biological species (e.g., proteins, cells, and micro-organisms) from complex samples because they can be easily manipulated by magnetic fields and require no special and expensive instruments. In this manner, magnetic immunoassays can provide a fast and simple technique to determine the presence or absence of the species. In such assays, various signal-generating mechanisms have been used, including color (absorption and reflectance), fluorescence, chemilluminescence, radioactivity and enzymes.

[0005] However, conventional magnetic immunoassays generally require control samples to generate a calibration curve each time they are used to obtain quantitative information for analytes. Specifically, when analyzing the presence or absence of a biological species within a test sample, multiple control samples are simultaneously tested for known amounts of the species in an attempt to calibrate the test assay at approximately the same conditions. Unfortunately, this calibration technique is often inconvenient, costly, and cumbersome on the tester.

[0006] As such, a need currently exists for an accurate calibration system for assays that is readily controllable and relatively inexpensive.

SUMMARY OF THE INVENTION

[0007] In accordance with one embodiment of the present invention, a fluidics-based assay device (e.g., capillary device) for detecting the presence or quantity of an analyte residing in a test sample is disclosed. The device comprises a reaction chamber that is being capable of containing a solution that comprises the test sample, detection probes capable of generating a detection signal, and magnetic calibration probes capable of generating a calibration signal. Generally speaking, the detection probes and calibration probes may be formed from any material that is capable of generating a detectable signal. For example, in some embodiments, such probes are selected from the group consisting of chromogens, catalysts, fluorescent compounds, chemiluminescent compounds, phosphorescent compounds, radioactive compounds, direct visual labels, liposomes, and combinations thereof. For instance, the detection probes and calibration probes may be fluorescent compounds, such as fluorescent particles. In one particular embodiment, the detection probes are fluorescent non-magnetic compounds and the calibration probes are fluorescent magnetic particles. If desired, the fluorescent magnetic particles may be conjugated with a specific binding member or blocked.

[0008] A channel is in fluid communication with the reaction chamber that defines a detection zone. In one embodiment, the channel facilitates capillary flow of the solution through the device. If desired, a barrier may be disposed between the reaction chamber and the channel to hold the solution within the reaction chamber for a certain period of time. In one embodiment, for example, the barrier is capable of being substantially dissolved by the solution. Such a barrier may contain a material selected from the group consisting of carbohydrates; (e.g., sucrose, glucose, etc.), salts (sodium chloride, etc.); and combinations thereof. In another embodiment, the barrier may be capable of physically rupturing.

[0009] A magnetic device is positioned adjacent to the detection zone to separate the detection probes and the calibration probes from the solution. For example, in one embodiment of a sandwich assay format, the detection probes and calibration probes form complexes with the analyte while in the reaction chamber. When placed into communication with the magnetic device at the detection zone, these analyte complexes and any uncomplexed calibration probes are separated from the solution.

[0010] The separated detection and calibration probes (complexed and/or uncomplexed) are thus capable of indicating the presence or quantity of analyte in the test sample. Specifically, the amount of the analyte within the test sample is proportional to the intensity of the detection signal generated by the separated detection probes (complexed and/or uncomplexed) at the detection zone calibrated by the intensity of the calibration signal generated by the separated calibration probes (complexed and/or uncomplexed) at the detection zone. For example, in one embodiment, the amount of the analyte within the test sample is proportional to the intensity of the detection signal divided by the intensity of the calibration signal.

[0011] In accordance with another embodiment of the present invention, a method for detecting the presence or quantity of an analyte residing in a test sample is disclosed. The method comprises:

[0012] i) providing a fluidics-based device, the device comprising:

[0013] a) a reaction chamber containing detection probes capable of generating a detection signal and magnetic calibration probes capable of generating a calibration signal;

[0014] b) a channel in fluid communication with the reaction chamber that defines a detection zone; and

[0015] c) a magnetic device positioned adjacent to the detection zone;

[0016] ii) applying a test sample containing the analyte to the reaction chamber to form a solution;

[0017] iii) allowing the solution to flow from the reaction chamber to the detection zone of the channel;

[0018] iv) separating the detection probes and the calibration probes from the solution at the detection zone using the magnetic device;

[0019] v) exciting the separated detection probes (complexed and/or uncomplexed) and the separated calibration probes (complexed and/or uncomplexed), wherein the excitation causes the separated detection probes to emit the detection signal and the separated calibration probes to emit the calibration signal;

[0020] vi) measuring the intensity of the detection signal at a first emission wavelength and the intensity of the calibration signal at a second emission wavelength, which may be the same or different than the first emission wavelength; and

[0021] vii) comparing the intensity of the detection signal to the calibration signal, wherein the amount of the analyte within the test sample is proportional to the intensity of the detection signal calibrated by the intensity of the calibration signal.

[0022] The separated detection probes and calibration probes may be excited simultaneously or separately. Likewise, the intensity of the detection signal and the calibration signal may be measured simultaneously or separately. Further, in one embodiment, the method further comprises generating a calibration curve by plotting the intensity of the detection signal calibrated by the intensity of the calibration signal for a plurality of predetermined analyte concentrations.

[0023] Other features and aspects of the present invention are discussed in greater detail below.

BRIEF DESCRIPTION OF THE DRAWINGS

[0024] A full and enabling disclosure of the present invention, including the best mode thereof, directed to one of ordinary skill in the art, is set forth more particularly in the remainder of the specification, which makes reference to the appended figures in which:

[0025]FIG. 1 is a perspective view of one embodiment of a fluidics-based device of the present invention;

[0026]FIG. 2 is a graphical illustration of the mechanism used for one embodiment of a sandwich assay format of the present invention;

[0027]FIG. 3 is a graphical illustration of the mechanism used for another embodiment of a sandwich assay format of the present invention;

[0028]FIG. 4 is a graphical illustration of the mechanism used for one embodiment of a competitive assay format of the present invention;

[0029]FIG. 5 is a graphical illustration of the mechanism used for another embodiment of a competitive assay format of the present invention;

[0030]FIG. 6 is a graphical illustration of one embodiment for covalently conjugating an antibody to carboxylate nanoparticles;

[0031]FIG. 7 shows the excitation (EX) and emission (EM) spectra of a calibration probe (C) and a detection probe (FP) in accordance with one embodiment of the present invention;

[0032]FIG. 8 shows the normalized fluorescent intensity versus the amount of leutinizing harmone (LH) as discussed in Example 1;

[0033]FIG. 9 shows the normalized fluorescent intensity versus the amount of leutinizing harmone (LH) as discussed in Example 2; and

[0034]FIG. 10 shows the normalized fluorescent intensity versus the amount of C-reactive protein (CRP) as discussed in Example 4.

[0035] Repeat use of reference characters in the present specification and drawings is intended to represent same or analogous features or elements of the invention.

DETAILED DESCRIPTION OF REPRESENTATIVE EMBODIMENTS Definitions

[0036] As used herein, the term “analyte” generally refers to a substance to be detected. For instance, analytes can include antigenic substances, haptens, antibodies, and combinations thereof. Analytes include, but are not limited to, toxins, organic compounds, proteins, peptides, microorganisms, amino acids, nucleic acids, hormones, steroids, vitamins, drugs (including those administered for therapeutic purposes as well as those administered for illicit purposes), bacteria, virus particles and metabolites of or antibodies to any of the above substances. Specific examples of some analytes include ferritin; creatinine kinase MIB (CK-MB); digoxin; phenytoin; phenobarbitol; carbamazepine; vancomycin; gentamycin; theophylline; valproic acid; quinidine; leutinizing hormone (LH); follicle stimulating hormone (FSH); estradiol, progesterone; IgE antibodies; vitamin B2 micro-globulin; glycated hemoglobin (Gly. Hb); cortisol; digitoxin; N-acetylprocainamide (NAPA); procainamide; antibodies to rubella, such as rubella-IgG and rubella IgM; antibodies to toxoplasmosis, such as toxoplasmosis IgG (Toxo-IgG) and toxoplasmosis IgM (Toxo-IgM); testosterone; salicylates; acetaminophen; hepatitis B virus surface antigen (HBsAg); antibodies to hepatitis B core antigen, such as anti-hepatitis B core antigen IgG and IgM (Anti-HBC); human immune deficiency virus 1 and 2 (HIV 1 and 2); human T-cell leukemia virus 1 and 2 (HTLV); hepatitis B e antigen (HBeAg); antibodies to hepatitis B e antigen (Anti-HBe); thyroid stimulating hormone (TSH); thyroxine (T4); total triiodothyronine (Total T3); free triiodothyronine (Free T3); carcinoembryoic antigen (CEA); and alpha fetal protein (AFP). Drugs of abuse and controlled substances include, but are not intended to be limited to, amphetamine; methamphetamine; barbiturates, such as amobarbital, secobarbital, pentobarbital, phenobarbital, and barbital; benzodiazepines, such as librium and valium; cannabinoids, such as hashish and marijuana; cocaine; fentanyl; LSD; methaqualone; opiates, such as heroin, morphine, codeine, hydromorphone, hydrocodone, methadone, oxycodone, oxymorphone and opium; phencyclidine; and propoxyhene. Other potential analytes may be described in U.S. Pat. No. 4,366,241 to Tom et al.

[0037] As used herein, the term “test sample” generally refers to a material suspected of containing the analyte. The test sample can be used directly as obtained from the source or following a pretreatment to modify the character of the sample. The test sample can be derived from any biological source, such as a physiological fluid, including, blood, saliva, ocular lens fluid, cerebral spinal fluid, sweat, urine, milk, ascites fluid, raucous, synovial fluid, peritoneal fluid, amniotic fluid or the like. The test sample can be pretreated prior to use, such as preparing plasma from blood, diluting viscous fluids, and the like. Methods of treatment can involve filtration, distillation, concentration, inactivation of interfering components, and the addition of reagents. Besides physiological fluids, other liquid samples can be used such as water, food products and the like for the performance of environmental or food production assays. In addition, a solid material suspected of containing the analyte can be used as the test sample. In some instances it may be beneficial to modify a solid test sample to form a liquid medium or to release the analyte.

DETAILED DESCRIPTION

[0038] Reference now will be made in detail to various embodiments of the invention, one or more examples of which are set forth below. Each example is provided by way of explanation of the invention, not limitation of the invention. In fact, it will be apparent to those skilled in the art that various modifications and variations can be made in the present invention without departing from the scope or spirit of the invention. For instance, features illustrated or described as part of one embodiment, can be used on another embodiment to yield a still further embodiment. Thus, it is intended that the present invention covers such modifications and variations as come within the scope of the appended claims and their equivalents.

[0039] In general, the present invention is directed to a fluidics-based assay device for detecting the presence or quantity of an analyte residing in a test sample. The device utilizes a self-calibrated magnetic binding assay system (e.g., sandwich, competitive, etc.) that includes detection probes capable of generating a detection signal (e.g., fluorescent non-magnetic particles) and calibration probes capable of generating a calibration signal (e.g., fluorescent magnetic particles). The amount of the analyte within the test sample is proportional (e.g., directly or inversely) to the intensity of the detection signal calibrated by the intensity of the calibration signal. It has been discovered that the fluidics-based device of the present invention provides an accurate, inexpensive, and readily controllable method of determining the presence of an analyte in a test sample.

[0040] Referring to FIGS. 1-2, for instance, one embodiment of a fluidics-based device 20 that can be formed according to the present invention will now be described in more detail. As shown in FIG. 1, the device 20 has a reaction chamber 12 in fluid communication with a fluidic channel 14. Although the reaction chamber 12 and the fluidic channel 14 are shown in a substantial linear relationship, it should be understood that the chamber 12 and channel 14 may also be disposed in other relationships as well. Further, it should also be understood that the reaction chamber 12 and the fluidic channel 14 may be the same or different. For instance, in one embodiment, the fluidic channel and reaction chamber may both be defined by one fluidic cavity.

[0041] To initiate the detection of an analyte within the test sample, the test sample is applied to the reaction chamber 12. Alternatively, the test sample may be applied to a sampling chamber (not shown) that is in fluid communication with the reaction chamber 12. To facilitate detection of the presence or absence of an analyte within the test sample, various detection probes 41 are also contained within the reaction chamber 12. These probes 41 remain available for binding with the analyte while contained within the reaction chamber 12. Upon binding with the analyte, the probes 41 can later serve to identify the presence or absence of the analyte. The detection probes 41 may be used for both detection and calibration of the device 20. In alternative embodiments, however, separate calibration probes 43 can also be applied to the reaction chamber 12 for use in conjunction with the detection probes 41 to facilitate simultaneous calibration and detection, thereby eliminating inaccuracies often created by conventional assay calibration systems. It should be understood, however, that the detection probes 41 and/or the calibration probes 43 may be applied together or separately at any location of the capillary flow device 20. Further, other compounds may also be added to the reaction chamber 12, such as to facilitate the suspension or mixing of the reagents.

[0042] Any substance generally capable of generating a signal that is detectable visually or by an instrumental device may be used as the detection probes 41 and/or the calibration probes 43. Various suitable substances can include chromogens; catalysts; fluorescent compounds; chemiluminescent compounds; phosphorescent compounds; radioactive compounds; direct visual labels, including colloidal metallic (e.g., gold) and non-metallic particles, dye particles, enzymes or substrates, or organic polymer latex particles; liposomes or other vesicles containing signal producing substances; and the like. For instance, some enzymes suitable for use as probes are disclosed in U.S. Pat. No. 4,275,149 to Litman, et al., which is incorporated herein in its entirety by reference thereto for all purposes. One example of an enzyme/substrate system is the enzyme alkaline phosphatase and the substrate nitro blue tetrazolium-5-bromo-4-chloro-3-indolyl phosphate, or derivative or analog thereof, or the substrate 4-methylumbelliferyl-phosphate. Other suitable probes may be described in U.S. Pat. No. 5,670,381 to Jou, et al. and U.S. Pat. No. 5,252,459 to Tarcha, et al., which are incorporated herein in their entirety by reference thereto for all purposes.

[0043] In some embodiments, the detection probes 41 and/or the calibration probes 43 can contain a fluorescent compound that produces a detectable signal. The fluorescent compounds can be fluorescent molecules, polymers, dendrimers, particles, and the like. Some examples of suitable fluorescent molecules, for instance, include, but are not limited to, fluorescein, europium chelates, phycobiliprotein, rhodamine and their derivatives and analogs. Moreover, some commercially available examples of suitable fluorescent particles include fluorescent carboxylated microspheres sold by Molecular Probes, Inc. under the trade names “FluoSphere” (Red 580/605) and “TransfluoSphere” (543/620), as well as “Texas Red” and 5- and 6-carboxytetramethylrhodamine, which are also sold by Molecular Probes, Inc.

[0044] Regardless of the technique used to impart the probe with a signal generating capability, it is typically desired that the detection probes 41 and/or the calibration probes 43 be magnetically responsive probes. Generally, a material is considered “magnetically responsive” or “magnetic” if it is influenced by the application of a magnetic field, such as, for example, if it is attracted or repulsed or has a detectable magnetic susceptibility or induction. For instance, some examples of suitable magnetically responsive materials that can be used to impart magnetic properties to a probe include, but are not limited to, paramagnetic materials, superparamagnetic materials, ferromagnetic materials, ferrimagnetic materials, and metamagnetic materials. Specific examples are metals such as iron, nickel, cobalt, chromium, manganese, and the like; lanthanide elements such as neodymium, erbium, and the like; alloys such as magnetic alloys of aluminum, nickel, cobalt, copper and the like; oxides such as ferric oxide (Fe₃O₄), ferrous oxide (Fe₂O₃), chromium oxide (CrO₂), cobalt oxide (CoO), nickel oxide (NiO₂), manganese oxide (Mn₂O₃) and the like; composite materials such as ferrites and the like; and solid solutions such as magnetite with ferric oxide and the like.

[0045] In some embodiments, the detection probes 41 and/or the calibration probes 43 are fluorescent and magnetic. Fluorescent magnetic probes are generally well known in the art and often include a magnetically responsive component and a fluorescent component. In some embodiments, for example, one or more fluorescent dyes can be applied to magnetic particles to form the probes, while in other embodiments, fluorescent dye(s) can be applied to non-magnetic particles that are coupled with magnetic particles. Some examples of suitable fluorescent dyes include, but are not limited to, monomethine dyes, trimethine dyes, pentamethine dyes, quinoline dyes, squaric acid-based dyes, and the like. The monomethine dyes that are pyridines typically have a blue or blue-green fluorescence emission, while quinolines typically have a green or yellow-green fluorescence emission. The trimethine dyes are substantially shifted toward red wavelengths, while the pentamethine dyes are shifted even further, often exhibiting infrared fluorescence emission. Specific examples of such fluorescent dyes include, but are not limited to, phthalocyanines, 2,3-naphthalocyanines, squaraines and croconic acid derivatives. Other examples of suitable fluorescent magnetic particles are believed to be described in U.S. Pat. No. 4,731,337 to Luotola, et al. and U.S. Pat. No. 6,268,222 to Chandler, et al., which are incorporated herein in their entirety by reference thereto for all purposes.

[0046] When the detection probes 41 and/or the calibration probes 43 are particles, such as described above, the mean diameter of the particulate probes may generally vary as desired depending on factors such as the type of particle chosen, the pore size of the membrane, and the membrane composition. For example, in some embodiments, the mean diameter of the particulate probes can range from about 0.01 microns to about 1,000 microns, in some embodiments from, about 0.01 microns to about 100 microns, and in some embodiments, from about 0.01 microns to about 10 microns. In one particular embodiment, the particulate probes have a mean diameter of from about 1 to about 2 microns. Generally, the particles are substantially spherical in shape, although other shapes including, but not limited to, plates, rods, bars, irregular shapes, etc., are suitable for use in the present invention. As will be appreciated by those skilled in the art, the composition, shape, size, and/or density of the particles may widely vary.

[0047] The detection probes 41 and/or the calibration probes 43 may be capable of bonding (covalently or non-covalently) or physically adsorbing the analyte. However, it is often desired to modify the probes in some manner so that they are more readily able to bond to the analyte. In such instances, the detection probes 41 and/or the calibration probes 43 can be modified with certain specific binding members 90 a and/or 90 b (See FIG. 2) that are adhered thereto to form probe conjugates.

[0048] Specific binding members generally refer to a member of a specific binding pair, i.e., two different molecules where one of the molecules chemically and/or physically binds to the second molecule. For instance, immunoreactive specific binding members can include antigens, haptens, aptamers, antibodies, and complexes thereof, including those formed by recombinant DNA methods or peptide synthesis. An antibody can be a monoclonal or polyclonal antibody, a recombinant protein or a mixture(s) or fragment(s) thereof, as well as a mixture of an antibody and other specific binding members. The details of the preparation of such antibodies and their suitability for use as specific binding members are well known to those skilled in the art.

[0049] Other common specific binding pairs include but are not limited to, biotin and avidin, carbohydrates and lectins, complementary nucleotide sequences (including probe and capture nucleic acid sequences used in DNA hybridization assays to detect a target nucleic acid sequence), complementary peptide sequences including those formed by recombinant methods, effector and receptor molecules, hormone and hormone binding protein, enzyme cofactors and enzymes, enzyme inhibitors and enzymes, and the like. Furthermore, specific binding pairs can include members that are analogs of the original specific binding member. For example, a derivative or fragment of the analyte, i.e., an analyte-analog, can be used so long as it has at least one epitope in common with the analyte.

[0050] The specific binding members 90 a and/or 90 b can generally be attached to the probes 41 and/or 43 using any of a variety of well-known techniques. For instance, covalent attachment of the specific binding members 90 a and/or 90 b to the probes 41 and/or 43 (e.g., microparticles) can be accomplished using carboxylic, amino, aldehyde, bromoacetyl, iodoacetyl, thiol, epoxy and other reactive or linking functional groups, as well as residual free radicals and radical cations, through which a protein coupling reaction can be accomplished. A surface functional group can also be incorporated as a functionalized co-monomer because the surface of the microparticle can contain a relatively high surface concentration of polar groups. In addition, although microparticle probes are often functionalized after synthesis, in certain cases, such as poly(thiophenol), the microparticles are capable of direct covalent linking with a protein without the need for further modification. For example, referring to FIG. 6, one embodiment of the present invention for covalently conjugating a probe is illustrated. As shown, the first step of conjugation is activation of carboxylic groups on the probe surface using carbodiimide. In the second step, the activated carboxylic acid groups are reacted with an amino group of an antibody to form an amide bond. The activation and/or antibody coupling can occur in a buffer, such as phosphate-buffered saline (PBS) (e.g., pH of 7.2) or 2-(N-morpholino) ethane sulfonic acid (MES) (e.g., pH of 5.3). As shown, the resulting probes can then be blocked with ethanolamine, for instance, to form the probe conjugate. Besides covalent bonding, other attachment techniques, such as adsorption, may also be utilized in the present invention.

[0051] Referring again to FIG. 1, a test sample containing an analyte can initially be applied to the reaction chamber 12 where the analyte mixes with the detection probes 41 and/or the calibration probes 43. Depending on the type of probes selected, the analyte may bind with the detection probes 41 and/or the calibration probes 43 to form complexes 49 (See FIG. 2). For instance, in one embodiment, a test sample containing an analyte is mixed with (1) fluorescent non-magnetic particles 41 conjugated with a first binding member 90 a and (2) fluorescent magnetic particles 43 conjugated with a second binding member 90 b. In such an instance, the analyte forms sandwich complexes 49 with the fluorescent non-magnetic particles 41 and the fluorescent magnetic particles 43.

[0052] Although not required, it is generally desired that the test sample be kept within the reaction chamber 12 long enough to allow for sufficient formation of the complexes 49. Thus, in one embodiment, a barrier 70 may be positioned between the reaction chamber 12 and fluidic channel 14. The barrier 70 may control the flow of fluids from the reaction chamber 12 to the fluidic channel 14 in a variety of ways. For example, in some embodiments, the barrier 70 is formed from a material that substantially dissolves in solution after a certain period of time. Examples of such dissolvable materials that may be used to form the barrier 70 include, but are not limited to, carbohydrates (e.g., sucrose, glucose, etc.); salts (e.g., sodium chloride, etc.); and the like. Alternatively, the barrier 70 may also be a physical barrier that is broken or otherwise ruptured after a period of time. Examples of such physical barriers include, but are not limited to, membranes, foils, thin silicone wafers, and the like. The rate of removal of the barrier 70, whether by dissolution or physical rupture, will generally depend on the material selected and the geometry of the barrier 70. For instance, in some embodiments, the length of the barrier 70 in the -x direction may range from about 1 micrometer to about 1 centimeter, and in some embodiments, from about 10 micrometer to about 1 millimeter.

[0053] Other techniques may also be utilized to control the time for which the test sample remains in the reaction chamber 12. For example, in some embodiments, the barrier 70 may be formed from a material that is generally hydrophobic such that it repels aqueous solutions, but that is also capable of being made sufficiently hydrophilic after a certain period of time to allow the passage of an aqueous solution. For example, the barrier 70 may contain a hydrophobic surface, such as found in polyethylene, polypropylene, polystyrene, polyacrylates, silicon elastomers and the like. In one embodiment, the binding of the probes and/or analyte within the reaction chamber 12 alters the hydrophobic barrier to a zone that is relatively hydrophilic. Creation of the hydrophilic surface allows the test sample to flow from the reaction chamber 12 to the fluidic channel 14. Thus, fluid flow through the remainder of the device 20 is not affected once the barrier 70 has been made hydrophilic. Examples of such a hydrophobic/hydrophilic barrier are described in U.S. Pat. No. 5,885,527 to Buechler, which is incorporated herein in its entirety by reference thereto for all purposes. In addition to the time-delay devices described above, various other devices for delaying the flow of fluids may also be described in U.S. Pat. No. 4,426,451 to Columbus; U.S. Pat. No. 4,435,504 to Zuk, et al., U.S. Pat. No. 4,727,019 to Valkirs, et al., U.S. Pat. No. 4,857,453 to Ullman, et al., U.S. Pat. No. 4,877,586 to Devaney, Jr., et al.; U.S. Pat. No. 4,916,056 to Brown III, et al.; and U.S. Pat. No. 4,963,498 to Hillman, et al.

[0054] After a sufficient reaction time within the chamber 12, the complexes 49 and any unbound probes 41 and/or 43 may then travel through a fluidic channel 14 to a detection zone 31. If desired, the geometry of the fluidic channel 14 may be selected so that capillary forces assist the flow of the test sample from the reaction chamber 12 to the fluidic channel 14. For example, in some embodiments, the fluidic channel 14 may have a width in the -y direction that is from about 1 micrometer to about 5 centimeters, and in some embodiments, from about 50 micrometers to about 500 micrometers. Further, the fluidic channel 14 may have a length in the -x direction that is from about 1 millimeter to about 50 centimeters, and in some embodiments, from about 10 millimeters to about 50 millimeters. The fluidic channel 14 may also have a height in the -z direction that is from about 0.1 micrometers to about 50 millimeters, and in some embodiments, from about 5 micrometers to about 500 micrometers.

[0055] At the detection zone 31, the complexes 49 and any unbound conjugated, fluorescent magnetic particles 43 are then captured by a magnetic device 60 and separated from the rest of the sample using conventional techniques. A magnetic field generator, for instance, can be used to generate a magnetic field that elicits a response from the magnetically responsive probes. Suitable magnetic field generators include, but are not limited to, permanent magnets and electromagnets. The magnetic separation process typically involves mixing the sample with the magnetic particles in a liquid medium to bind the analyte by affinity reaction, and then separating the unbound magnetic particles and analyte complexes from the sample medium by applying a magnetic field. Most, if not all of the magnetic particles, except those particles that are colloidal, settle in time. The liquid medium, therefore, can be agitated to keep the particles suspended for a sufficient period of time to allow the bioaffinity binding reaction to occur. Examples of known agitation methods include shaking, swirling, rocking, rotation, or similar manipulations of a partially filled container. Some commercially available examples of suitable magnetic separation devices include the Dynal MPC series of separators manufactured by Dynal, Inc., Lake Success, N.Y., which employ a permanent magnet located externally to a container holding a test medium and provide only for separation. Mixing of the magnetic particles in the test medium for affinity binding reaction is done separately. In addition, other methods for capturing magnetic particles may be described in U.S. Pat. No. 5,200,084 to Liberti, et al.; U.S. Pat. No. 5,647,994 to Tuunanen, et al.; U.S. Pat. No. 5,795,470 to Wang, et al.; and U.S. Pat. No. 6,033,574 to Siddigi, which are incorporated herein in their entirety by reference thereto for all purposes.

[0056] Once captured, the fluorescence signal of the fluorescent magnetic particles 43, complexed and uncomplexed, and the complexes 49 can be measured using conventional techniques. For example, in one embodiment, the particles 43 and complexes 49 can be excited with the same external source. In this embodiment, the source supplies radiation at an excitation wavelength, thereby causing the particles 43 to emit light at a wavelength that is different than the wavelength emitted by the complexes 49. This enables the presence of the complexes 49 and particles 41 to be separately measured. Alternatively, the particles 43 and complexes 49 can also be measured separately using separate external sources.

[0057] Generally speaking, fluorescence is the result of a three-stage process that occurs in certain fluorescent compounds. In the first stage, energy is supplied by an external source, such as an incandescent lamp or a laser and absorbed by the fluorescent compound, creating an excited electronic singlet state. In the second stage, the excited state exists for a finite time during which the fluorescent compound undergoes conformational changes and is also subject to a multitude of possible interactions with its molecular environment. During this time, the energy of the excited state is partially dissipated, yielding a relaxed state from which fluorescence emission originates. The third stage is the fluorescence emission stage wherein energy is emitted, returning the fluorescent compound to its ground state. The emitted energy is lower than its excitation energy (light or laser) and thus of a longer wavelength. This shift or difference in energy or wavelength allows the emission energy to be detected and isolated from the excitation energy.

[0058] Fluorescence detection generally utilizes wavelength filtering to isolate the emission photons from the excitation photons, and a detector that registers emission photons and produces a recordable output, usually as an electrical signal or a photographic image. There are generally four recognized types of detectors: spectrofluorometers and microplate readers; fluorescence microscopes; fluorescence scanners; and flow cytometers. One suitable fluorescence detector for use with the present invention is a FluoroLog III Spectrofluorometer, which is sold by SPEX Industries, Inc. of Edison, N.J.

[0059] Although not required, the selection criteria of particularly desired detection and calibration probe pairs include: (1) little or no spectral overlap for either the absorption spectra or the fluorescence spectra so that emission intensities can be measured separately; (2) no significant fluorescent energy transfer between the detection and calibration probes when brought into a close proximity so that they emit independently; and (3) relatively long emission wavelength (e.g., greater than about 600 nm) so that the autofluorescence of biological fluids has a minimal effect on the fluorescence measurement. FIG. 7, for example, illustrates an exemplary calibration probe and detection probe having excitation spectra with little overlap so that they can be independently excited.

[0060] Further, if desired, a technique known as “time-resolved fluorescence detection” may also be utilized in the present invention. Time-resolved fluorescence detection is designed to reduce background signals from the emission source or from scattering processes (resulting from scattering of the excitation radiation) by taking advantage of the fluorescence characteristics of certain fluorescent materials, such as lanthanide chelates of europium (Eu (III)) and terbium (Tb (III)). Such chelates can exhibit strongly red-shifted, narrow-band, long-lived emission after excitation of the chelate at substantially shorter wavelengths. Typically, the chelate possesses a strong ultraviolet absorption band due to a chromophore located close to the lanthanide in the molecule. Subsequent to light absorption by the chromophore, the excitation energy can be transferred from the excited chromophore to the lanthanide. This is followed by a fluorescence emission characteristic of the lanthanide. The use of pulsed excitation and time-gated detection, combined with narrow-band emission filters, allows for specific detection of the fluorescence from the lanthanide chelate only, rejecting emission from other species present in the sample that are typically shorter-lived or have shorter wavelength emission. Other time-resolved techniques for measuring fluorescence are described in U.S. Pat. No. 5,585,279 to Davidson and U.S. Pat. No. 5,637,509 to Hemmila, et al., which are incorporated herein in their entirety by reference thereto for all purposes.

[0061] Regardless of the technique used to measure fluorescence, the absolute amount of the analyte can be ascertained by comparing the fluorescence signal of the captured, fluorescent non-magnetic particles 41 with the captured, fluorescent magnetic particles 43. The fluorescence intensity of the captured, fluorescent non-magnetic particles 41, I_(s), can be compared to the fluorescence intensity of the captured, fluorescent magnetic particles 43, I_(c). The total amount of the captured fluorescent magnetic particles 43 is predetermined and known and thus can be used for calibration purposes. For example, in one embodiment, the amount of analyte is directly proportional to the ratio of I_(s) to I_(c). Based upon the intensity range in which the detection zone 31 falls, the general concentration range for the analyte may be determined. As a result, calibration and sample testing may be conducted under approximately the same conditions at the same time, thus providing reliable quantitative or semi-quantitative results, with increased sensitivity.

[0062] If desired, the ratio of I_(s) to I_(c) may be plotted versus the analyte concentration for a range of known analyte concentrations to generate a calibration curve. To determine the quantity of analyte in an unknown test sample, the signal ratio may then be converted to analyte concentration according to the calibration curve. It should be noted that the capturing efficiency of the complexed and uncomplexed fluorescent magnetic particles is generally the same for any given sample. Accordingly, the variation in capturing efficiency is not believed to significantly interfere with the results from sample-to-sample because the ratio of fluorescence intensities (i.e., I_(s)/I_(c)) is used instead of absolute fluorescence. It should also be noted that alternative mathematical relationships between I_(s) and I_(c) may be plotted versus the analyte concentration to generate the calibration curve. For example, in one embodiment, the value of I_(s)/(I_(s)+I_(c)) may be plotted versus analyte concentration to generate the calibration curve.

[0063] Referring again to FIG. 1, any probes or complexes that are not bound at the detection zone 31 continue along the fluidic channel 14 until they encounter a wicking pad 28 and accumulate thereon. Although not required, the wicking pad 28 may assist in promoting capillary action and fluid flow through the device 20. Some suitable materials that can be used to form the wicking pad 28 include, but are not limited to, nitrocellulose, cellulose, porous polyethylene pads, and glass fiber filter paper.

[0064] Various other embodiments are also contemplated by the present invention. For instance, referring to FIG. 3, the device 20 described above and illustrated in FIG. 1 can be modified to form another format of a sandwich assay. In one embodiment, for instance, a test sample containing an analyte can initially be mixed with (1) fluorescent non-magnetic particles 141 a conjugated with a first binding member 190 a, (2) fluorescent magnetic particles 143, and (3) non-fluorescent magnetic particles 141 b conjugated with a second binding member 190 b. In this particular embodiment, the fluorescent magnetic particles 143 can be blocked with a blocking agent, such as β-casein, to prevent nonspecific binding to the analyte, thereby allowing such particles 143 to act only as a calibration probe. Further, the first specific binding member 190 a and the second specific binding member 190 b may be analogs of the analyte.

[0065] The term “blocking agent” means a reagent that adheres to the probe surface so that it “blocks” or prevents non-analyte materials from binding to the surface. Blockers can include, but are not limited to, β-casein, albumins such as bovine serum albumin, pluronic or other surfactants, polyethylene glycol, polyvinyl alcohol, or sulfur derivatives of the above compounds, and any other blocking material known to those of ordinary skill in the art.

[0066] Referring again to FIG. 3, the analyte forms sandwich complexes 149 with the conjugated, fluorescent non-magnetic particles 141 a and the conjugated, non-fluorescent, magnetic particles 141 b. The complexes 149 can migrate from the reaction chamber 12 to the detection zone 31 within the fluidic channel 14. At the detection zone 31, the complexes 149 and any unbound particles 143 and/or 141 b are then captured by the magnetic device 60 and separated from the rest of the sample. As described above, the absolute amount of the analyte can be ascertained by comparing the fluorescence intensity of the captured, fluorescent non-magnetic particles 141 a, I_(s), to the fluorescence intensity of the captured, fluorescent magnetic particles 143, I_(c). In particular, the total amount of the captured fluorescent magnetic particles 143 is predetermined and known and thus can be used for calibration purposes. Accordingly, the amount of analyte in this embodiment is directly proportional to the ratio of I_(s) to I_(c).

[0067] Moreover, referring to FIG. 4, the device 20 described above and illustrated in FIG. 1 can also be modified to form a competitive assay. In one embodiment, for instance, a test sample containing an analyte can initially be mixed with (1) fluorescent non-magnetic particles 241 conjugated with a first binding member 290 a and (2) fluorescent magnetic particles 243 conjugated with a second binding member 290 b. In this particular embodiment, the first binding member 290 a can be identical to the analyte, while the second binding member 290 b can be an analog of the analyte.

[0068] Upon mixing, the analyte competes with the conjugated, fluorescent non-magnetic particles 241 for the conjugated, fluorescent magnetic particles 243 such that complexes 249 a of the analyte and the fluorescent magnetic particles 243 and complexes 249 b of the fluorescent magnetic particles 243 and the fluorescent, non-magnetic particles 241 are formed. The complexes 249 a and 249 b can migrate from reaction chamber 12 to the detection zone 31 present in the fluidic channel 14. At the detection zone 31, the complexes 249 a and 249 b and any unbound particles 243 are then captured by the magnetic device 60 and separated from the rest of the sample. As described above, the absolute amount of the analyte can be ascertained by comparing the fluorescence intensity of the captured, fluorescent non-magnetic particles 241, I_(s), to the fluorescence intensity of the captured, complexed or uncomplexed, fluorescent magnetic particles 243, I_(c). In particular, the total amount of the captured fluorescent magnetic particles 243 is predetermined and known and thus can be used for calibration purposes. Accordingly, the amount of analyte in this embodiment is inversely proportional to the ratio of I_(s) to I_(c).

[0069] Referring to FIG. 5, the device 20 described above and illustrated in FIG. 1 can also be modified to form another format of a competitive assay. In one embodiment, for instance, a test sample containing an analyte can initially be mixed with (1) fluorescent non-magnetic particles 341 a conjugated with a first binding member 390 a (2) fluorescent magnetic particles 343, and (3) non-fluorescent magnetic particles 341 b conjugated with a second binding member 390 b. In this particular embodiment, the first binding member 390 a can be identical to the analyte, while the second binding member 390 b can be an analog of the analyte. Further, the fluorescent magnetic particles 343 can be blocked with a blocking agent, such as β-casein, to prevent nonspecific binding to the analyte, thereby allowing such particles to act only as a calibration probe.

[0070] Upon mixing, the analyte competes with the conjugated, fluorescent non-magnetic particles 341 a for the conjugated, non-fluorescent magnetic particles 341 b such that complexes 349 a of the analyte and the non-fluorescent magnetic particles 341 b and complexes 349 b of the non-fluorescent magnetic particles 341 b and the fluorescent non-magnetic particles 341 a are formed. The complexes 349 a and 349 b can migrate from the reaction chamber 12 to the detection zone 31 present in the fluidic channel 14. At the detection zone 31, the complexes 349 a and 349 b and any unbound particles 343 and/or 341 b are then captured by the magnetic device 60 and separated from the rest of the sample. As described above, the absolute amount of the analyte can be ascertained by comparing the fluorescence intensity of the captured, fluorescent non-magnetic particles 341 a, I_(s), to the fluorescence intensity of the captured, fluorescent magnetic particles 343, I_(c). In particular, the total amount of the captured fluorescent magnetic particles 343 is predetermined and known and thus can be used for calibration purposes. Accordingly, the amount of analyte in this embodiment is inversely proportional to the ratio of I_(s) to I_(c).

[0071] Although various embodiments of device configurations have been described above, it should be understood, that the device 20 may generally have any configuration desired. For example, the device 20 may contain multiple fluidic channels 14 and/or reaction chambers 12. In this manner, simultaneous detection of a larger number of analytes could be achieved using a single device 20. In addition, different assay formats may also be utilized for the device 20. For instance, a competitive assay may be formed such as shown in FIG. 4 and described above, except that the particles 241 are fluorescent, magnetic particles and the particles 243 are fluorescent, non-magnetic particles. Likewise, a competitive assay may be formed such as shown in FIG. 5 and described above, except that the particles 341 a are non-fluorescent, magnetic particles and the particles 341 b are fluorescent, non-magnetic particles. Various other device configurations and/or assay formats are also described in U.S. Pat. No. 4,596,695 to Cottingham; U.S. Pat. No. 5,145,784 to Cox, et al.; U.S. Pat. No. 5,395,754 to Lambotte, et al.; U.S. Pat. No. 5,670,381 to Jou, et al.; and U.S. Pat. No. 6,194,220 to Malick, et al., which are incorporated herein in their entirety by reference thereto for all purposes.

[0072] Moreover, although various embodiments have been described above that relate specifically to the use of fluorescence as the mechanism for calibration and detection, other well known detection mechanisms are equally applicable in the present invention. For example, in some embodiments, the detection and/or calibration probes may be chemiluminescent or phosphorescent compounds. Chemiluminescent probes, for instance, may be excited through the use of a suitable reactant as is well known in the art. Still other embodiments and configurations are also contemplated by the present invention.

[0073] The present inventors have discovered that the fluidics-based assay device of the present invention can be utilized to manipulate magnetic probes and establish separation and detection of an analyte. Specifically, magnetic separation and detection techniques (e.g., fluorescence) are built into an integrated system. Further, the system is self-calibrated to eliminate the requirement of control calibration samples when using conventional external calibration techniques. In one-embodiment, self-calibration is accomplished through the use of fluorescent magnetic probes. The fluorescence emitted from the fluorescent magnetic probes and fluorescent non-magnetic probes can be separately measured on the same sample. Because the number of magnetic particles is predetermined, the system is self-calibrated when determining the amount of the captured fluorescent non-magnetic probes, and subsequently, the amount of analyte. Furthermore, because the fluorescence of the calibration and detection probes are simultaneously measured under identical conditions, potential interference from many variations, such as temperature and instrument instability, can be avoided to improve detection reliability and consistency.

[0074] The present invention may be better understood with reference to the following examples.

EXAMPLE 1

[0075] The ability to detect the presence of an analyte using a sandwich assay, such as shown in FIG. 3, was demonstrated. Initially, the following components were added to six Eppendorf vials:

[0076] (1) 25 microliters of covalently conjugated, non-fluorescent magnetic particles (3 milligrams per milliliter in PBS buffer);

[0077] (2) 15 microliters of covalently conjugated, fluorescent non-magnetic particles (2 milligrams per milliliter in PBS buffer);

[0078] (3) 10 microliters of fluorescent magnetic particles blocked by β-casein (3 milligrams per milliliter in PBS buffer); and

[0079] (4) Leutinizing hormone (LH) analyte ranging from 0, 10 microliters (1 microgram per milliliter), 20 microliters (1 microgram per milliliter), 40 microliters (1 microgram per milliliter), 40 microliters (2 micrograms per milliliter) and 80 microliters (2 micrograms per milliliter).

[0080] To each of the Eppendorf vials, an appropriate amount of PBS buffer was added to a final volume of 150 microliters. The samples were incubated at room temperature for 10 minutes with gentle shaking. The magnetic particles were then separated by a magnetic separator obtained from Dynal, Inc. The supernatant from each vial was discarded and the magnetic particles were re-suspended in 1.5 milliliters of PBS. 300 microliters of the fluorescent magnetic particle suspension was used for each fluorescence measurement. A “Flourolog III Spectrofluorometer”, which was obtained from SPEX Industries, Inc. of Edison, N.J., was used to measure the fluorescence of the sample using a right angle mode. An excitation wavelength of 470 nanometers and an emission wavelength of 560 nanometers were used for the fluorescent magnetic particles, while an excitation wavelength of 570 nanometers and an emission wavelength of 605 nanometers were used for the fluorescent, non-magnetic particles. The integration time was 0.2 seconds.

[0081] The normalized and calibrated fluorescence intensity as a function of the dose of LH in each sample is shown in FIG. 8. Normalized intensity was obtained by dividing the measured fluorescence intensity of the sample by the fluorescence intensity of a control sample. The control sample was the sample without the analyte.

[0082] The particles used in Example 1 were formed as follows:

[0083] Non-Fluorescent Magnetic Particles

[0084] 125 microliters of 10% carboxylate-modified paramagnetic particles (0.35 microns, Estapor® Superparamagnetic microspheres, obtained from Bang's Laboratories, Inc.) were washed once with 1.5 milliliters of carbonate buffer and twice with PBS using a magnetic separator. The washed particles were resuspended in 0.6 milliliters PBS and 15 milligrams carbodiimide (from Polysciences, Inc.). The mixture was allowed to react at room temperature (RT) for 30 minutes on a shaker. The activated particles were then washed twice with a borate buffer. The activated particles were again re-suspended in 1.2 milliliters of a borate buffer. Thereafter, 30 microliters of LH β-monoclonal antibody (9.8 mg/ml, obtained from Fitzgerald Industries International, Inc.) was added to the activated particles. The reaction mixture was allowed to react at room temperature on a shaker overnight. The activated particles were then collected and incubated in 1 milliliter of 0.1 molar ethanolamine under gentle shaking for 15 minutes. The particles were then washed twice with PBS and stored at 4° C. in a buffer that contained 0.1 molar PBS, 0.15 molar NaCl, 1% β-casein, 5% glycerol and 0.1% NaN₃.

[0085] Fluorescent Non-Magnetic Particles

[0086] The “fluorescent non-magnetic” particles were covalently conjugated according to the procedure described above, except that the binding member was LH α-monoclonal antibody (9.8 milligrams per milliliter, obtained from Fitzgerald Industries International, Inc.) instead of LH β-monoclonal antibody. The particles utilized were FluoSpheres® carboxylate-modified microspheres, which were obtained from Molecular Probes, Inc. The particles had a particle size of 0.5 microns, and were red fluorescent with an excitation wavelength of 580 nanometers and an emission wavelength of 605 nanometers.

[0087] Fluorescent Magnetic Particles

[0088] 100 microliters of a 2.76% solids suspension of fluorescent superparamagnetic particles (obtained from Polysciences, Inc. of Warrington, Pa.) were combined with 1 milliliter of a borate buffer (0.1 molar, pH 8.5) in an Eppendorf tube. Such particles have a mean diameter of between 1 to 2 microns and are believed to be iron-containing microspheres that have a polystyrene surface that allows for passive adsorption and functional group reactions with proteins. The particles were separated by a magnetic separator obtained from Dynal, Inc. and re-suspended in 200 microliters of a 10 milligram per milliliter solution of β-casein in a 0.1 molar borate buffer. The suspension was incubated for 30 minutes with gentle mixing. The above step was repeated twice. The separated particles were re-suspended in 200 microliters of PBS and stored at 4° C.

[0089] Leutinizing Hormone (LH)

[0090] The “leutinizing hormone (LH)” was obtained from Fitzgerald Industries International, Inc.

EXAMPLE 2

[0091] The ability to detect the presence of an analyte using a sandwich assay, such as shown in FIG. 2, was demonstrated. Initially, the following components were added to six Eppendorf vials:

[0092] (1) 5 microliters of covalently conjugated, fluorescent non-magnetic particles (2 milligrams per milliliter in PBS buffer);

[0093] (2) 15 microliters of physical absorption conjugated, fluorescent magnetic particles (3 milligrams per milliliter in PBS buffer); and

[0094] (3) Leutinizing hormone (LH) analyte ranging from 0, 5, 10 microliters, 20, 40, and 100 microliters (2 micrograms per milliliter).

[0095] To each of the Eppendorf vial, an appropriate amount of PBS buffer was added to a final volume of 150 microliters. The samples were incubated at room temperature for 25 minutes with gentle shaking. The magnetic particles were then separated by a magnetic separator obtained from Dynal, Inc. The supernatant from each vial was discarded and the magnetic particles were re-suspended in 1.5 milliliters of PBS. 300 microliters of the fluorescent magnetic particle suspension was used for each fluorescence measurement. A “Flourolog III Spectrofluorometer”, which was obtained from SPEX Industries, Inc. of Edison, N.J., was used to measure the fluorescence of the sample using a right angle mode. An excitation wavelength of 470 nanometers and an emission wavelength of 560 nanometers were used for the fluorescent magnetic particles, while an excitation wavelength of 570 nanometers and an emission wavelength of 605 nanometers were used for the fluorescent, non-magnetic particles. The integration time ranged from 0.2 to 1 second.

[0096] The normalized and calibrated fluorescence intensity as a function of the dose of LH in each sample is shown in FIG. 9.

[0097] The particles used in Example 2 were formed as follows:

[0098] Fluorescent Non-Magnetic Particles

[0099] The “fluorescent non-magnetic” particles were formed as described above in Example 1.

[0100] Fluorescent Magnetic Particles

[0101] 2.76 milligrams of fluorescent superparamagnetic particles (2.5% solids in an aqueous suspension) were obtained from Polysciences, Inc. of Warrington, Pa. The particles were washed three times with borate buffers and separated by a magnetic separator obtained from Dynal, Inc. The washed particles were re-suspended in a 200-microliter borate buffer, and 82 micrograms of β-leutinizing hormone (β-LH) monoclonal antibody (1 milligram per milliliter, obtained from Fitzgerald Industries International, Inc.) were added. The mixture was gently mixed overnight at room temperature. The particles were then collected by a magnetic separator and incubated with 200 microliters of β-casein (10 milligrams per milliliter in borate buffer) for 30 minutes with gentle mixing to block the nonspecific binding sites. The blocked particles were washed twice with PBS and stored in 0.1 molar PBS.

[0102] Leutinizing Hormone (LH)

[0103] The “leutinizing hormone (LH)” was obtained from Fitzgerald Industries International, Inc.

EXAMPLE 3

[0104] A self-calibrated magnetic binding assay was compared to a non-calibrated magnetic binding assay.

[0105] Without Self-Calibration

[0106] Initially, the following components were added to 5 Eppendorf vials (Vial Nos. 2-6 in Table I):

[0107] (1) 15 microliters of covalently conjugated, non-fluorescent magnetic particles (3 milligrams per milliliter in 0.1 molar PBS buffer);

[0108] (2) 15 microliters of covalently conjugated, fluorescent non-magnetic particles (2 milligrams per milliliter in PBS buffer);

[0109] (3) 20 microliters leutinizing hormone (LH) analyte (1 microgram per milliliter); and

[0110] (4) 20 microliters of PBS.

[0111] A control Eppendorf vial was also formed with only 20 microliters of PBS (Vial No. 1 in Table I).

[0112] The samples were incubated at room temperature for 20 minutes with gentle shaking. The magnetic particles were then separated by a magnetic separator obtained from Dynal, Inc. The supernatant from each vial was discarded and the magnetic particles were re-suspended in 1.5 milliliters of PBS. 300 microliters of the fluorescent magnetic particle suspension was used for each fluorescence measurement. A “Flourolog III Spectrofluorometer”, which was obtained from SPEX Industries, Inc. of Edison, N.J., was used to measure the fluorescence of the sample using a right angle mode. An excitation wavelength of 570 nanometers and an emission wavelength of 605 nanometers were used for to take fluorescence measurements on different days.

[0113] Table I lists the relative fluorescence data for each day. TABLE I Fluorescent Measurements Std. Vial No. 1 No. 2 No. 3 No. 4 No. 5 No. 6 Dev % Day 1 13 254 215 263 285 291 11 Day 2 12 235 207 300 263 299 15 Day 3 12 183 176 213 270 266 20 Day 4 18 265 226 275 282 293 10 Day 5 9 207 193 246 236 244 10 Day 6 14 227 202 252 262 274 12 Std. 23 13 8 11 6 7 Dev %

[0114] With Self-Calibration

[0115] Initially, the following components were added to 5 Eppendorf vials (Vial Nos. 9-13 in Table II):

[0116] (1) 15 microliters of covalently conjugated, non-fluorescent magnetic particles (3 milligrams per milliliter in 0.1 molar PBS buffer);

[0117] (2) 15 microliters of covalently conjugated, fluorescent non-magnetic particles (2 milligrams per milliliter in PBS buffer);

[0118] (3) 20 microliters of fluorescent magnetic particles blocked by β-casein (3 milligrams per milliliter in PBS buffer); and

[0119] (4) 20 microliters leutinizing hormone (LH) analyte (1 microgram per milliliter); and

[0120] (5) 20 microliters of PBS.

[0121] A control Eppendorf vial was also formed with only 20 microliters of PBS (Vial No. 8 in Table II).

[0122] The samples were incubated at room temperature for 20 minutes with gentle shaking. The magnetic particles were then separated by a magnetic separator obtained from Dynal, Inc. The supernatant from each vial was discarded and the magnetic particles were re-suspended in 1.5 milliliters of PBS. 300 microliters of the fluorescent magnetic particle suspension was used for each fluorescence measurement. The “Flourolog III Spectrofluorometer” was used to measure the fluorescence of the sample using a right angle mode. An excitation wavelength of 470 nanometers and an emission wavelength of 560 nanometers were used for the fluorescent magnetic particles, while an excitation wavelength of 570 nanometers and an emission wavelength of 605 nanometers were used for the fluorescent, non-magnetic particles. Table II lists the relative fluorescence data for each day. TABLE II Fluorescent Measurements Std. Vial No. 8 No. 9 No. 10 No. 11 No. 12 No. 13 Dev % Day 1 31/32 352/47 344/43 300/41 318/44 369/39 12 Day 2 31/42 324/42 329/41 323/46 338/47 418/43 14 Day 3 28/39 307/40 333/42 282/42 288/40 425/46 12 Day 4 30/41 267/36 292/36 271/41 281/38 356/43 8.8 Day 5 21/29 252/33 292/34 258/38 275/36 328/37 10 Day 6 21/25 237/33 307/38 265/40 288/35 358/39 12 Std. 13 3 3 4 5 6 Dev %

[0123] As can be seen from the comparisons of each set of samples for the two systems, the standard deviations (Std. Dev %) for the self-calibrated system were significantly smaller than the standard deviations without self-calibration, even under carefully controlled conditions. Because the self-calibrated system is less dependent on the measurement conditions, it is anticipated that the standard deviations for the self-calibrated system would be even smaller than the standard deviations without self-calibration when the conditions are not carefully controlled.

[0124] The particles used in Example 3 were formed as follows:

[0125] Non-Fluorescent Magnetic Particles

[0126] The “non-fluorescent magnetic” particles were formed as described above in Example 1.

[0127] Fluorescent Non-Magnetic Particles

[0128] The “fluorescent non-magnetic” particles were formed as described above in Example 1.

[0129] Fluorescent Magnetic Particles

[0130] The “fluorescent magnetic particles” were formed as described in Example 2.

[0131] Leutinizing Hormone (LH)

[0132] The “leutinizing hormone (LH)” was obtained from Fitzgerald Industries International, Inc.

EXAMPLE 4

[0133] The ability to detect the presence of an analyte using a sandwich assay, such as shown in FIG. 3, was demonstrated. Initially, the following components were added to six Eppendorf vials:

[0134] (1) 30 microliters of covalently conjugated, non-fluorescent magnetic particles (2 milligrams per milliliter in PBS buffer);

[0135] (2) 20 microliters of covalently conjugated, fluorescent non-magnetic particles (2 milligrams per milliliter in PBS buffer);

[0136] (3) 15 microliters of fluorescent magnetic particles blocked by β-casein (1 milligram per milliliter in PBS buffer); and

[0137] (4) C-reactive protein (CRP) analyte ranging from 0, 5, 10, 20, 50, and 100 microliters (0.2 micrograms per milliliter in PBS).

[0138] The samples were incubated at room temperature for 20 minutes with gentle shaking. The magnetic particles were then separated by a magnetic separator obtained from Dynal, Inc. The supernatant from each vial was discarded and the magnetic particles were re-suspended in 1.5 milliliter of PBS. 300 microliters of the fluorescent magnetic particle suspension was used for each fluorescence measurement. A “Flourolog III Spectrofluorometer”, which was obtained from SPEX Industries, Inc. of Edison, N.J., was used to measure the fluorescence of the sample using a right angle mode. An excitation wavelength of 470 nanometers and an emission wavelength of 560 nanometers were used for the fluorescent magnetic particles, while an excitation wavelength of 570 nanometers and an emission wavelength of 605 nanometers were used for the fluorescent, non-magnetic particles. The integration time ranged from 0.2 to 1 second. The normalized fluorescence intensity as a function of the dose of CRP in each sample is shown in FIG. 10.

[0139] The particles used in Example 4 were formed as follows:

[0140] Non-Fluorescent Magnetic Particles

[0141] 125 microliters of 10% carboxylate-modified paramagnetic particles (0.35 microns, Estapor® Superparamagnetic microspheres, available from Bang's Laboratories, Inc.) were washed once by 1.5 ml carbonate buffer and twice by phosphate buffer saline (PBS) using a magnetic separator. The washed particles were re-suspended in 0.6 milliliters PBS and 15 milligrams carbodiimide (from Polysciences, Inc.). The mixture was allowed to react at room temperature (RT) for 30 minutes on a shaker. The activated particles were then washed twice with a borate buffer. The activated particles were again re-suspended in 1.2 ml borate buffer. Thereafter, 30 microliters of anti-C-reactive protein (anti-CRP1) monoclonal antibody (Mab A5804, 2 mg/ml, obtained from BiosPacific, Inc.) were added to the activated particles. The reaction mixture was allowed to react at room temperature on a shaker overnight. The activated particles were then collected and incubated in 1 milliliter of 0.1 molar ethanolamine under gentle shaking for 15 minutes. The particles were then washed twice with PBS and stored at 4° C. in a buffer that contained 0.1 molar PBS, 0.15 molar NaCl, 1% β-casein, 5% glycerol and 0.1% NaN₃.

[0142] Fluorescent Non-Magnetic Particles

[0143] The “fluorescent non-magnetic” particles were covalently conjugated according to the procedure described above, except that the binding member was anti-C-reactive protein (anti-CRP2) monoclonal antibody (2 mg/ml, obtained from BiosPacific, Inc.) instead of anti-CRP1. The particles utilized were FluoSpheres® carboxylate-modified microspheres, which were obtained from Molecular Probes, Inc. The particles had a particle size of 0.5 βm, and were red fluorescent with an excitation wavelength of 580 nanometers and an emission wavelength of 605 nanometers.

[0144] Fluorescent Magnetic Particles

[0145] 100 microliters of a 2.76% solids suspension of fluorescent superparamagnetic particles (obtained from Polysciences, Inc. of Warrington, Pa.). Such particles have a mean diameter between 1 to 2 microns, and are believed to be iron-containing microspheres that have a polystyrene surface that allows for passive adsorption and functional group reactions with proteins. 1 milliliter of a borate buffer (0.1 molar, pH=8.5) was then added to the particles in an Eppendorf tube. The particles were separated by a magnetic separator obtained from Dynal, Inc. and the particles were re-suspended in 200 microliters of a 10 mg/ml solution of β-casein in a 0.1 M borate buffer. The suspension was incubated for 30 minutes with gentle mixing. The above step was repeated twice. The separated particles were re-suspended in 200 microliters of PBS and stored at 4° C.

[0146] C-Reactive Protein (CRP)

[0147] The “C-reactive protein (CRP)” was obtained BiosPacific, Inc.

[0148] While the invention has been described in detail with respect to the specific embodiments thereof, it will be appreciated that those skilled in the art, upon attaining an understanding of the foregoing, may readily conceive of alterations to, variations of, and equivalents to these embodiments. Accordingly, the scope of the present invention should be assessed as that of the appended claims and any equivalents thereto. 

What is claimed is:
 1. A fluidics-based assay device for detecting the presence or quantity of an analyte residing in a test sample, said device comprising: a reaction chamber, said reaction chamber being capable of containing a solution that comprises the test sample, detection probes capable of generating a detection signal, and magnetic calibration probes capable of generating a calibration signal; a channel in fluid communication with said reaction chamber, said channel defining a detection zone; and a magnetic device positioned adjacent to said detection zone, said magnetic device being capable of separating said detection probes and said calibration probes from said solution; wherein the amount of the analyte within the test sample is proportional to the intensity of the detection signal generated by said separated detection probes at the detection zone calibrated by the intensity of the calibration signal generated by said separated calibration probes at the detection zone.
 2. A device as defined in claim 1, wherein said channel facilitates capillary flow of the test sample.
 3. A device as defined in claim 1, further comprising a barrier disposed between said reaction chamber and said channel, said barrier being capable of holding said solution within said reaction chamber for a certain period of time.
 4. A device as defined in claim 3, wherein said barrier is capable of being substantially dissolved by said solution.
 5. A device as defined in claim 4, wherein said barrier contains a material selected from the group consisting of carbohydrates, salts, and combinations thereof.
 6. A device as defined in claim 3, wherein said barrier is capable of physically rupturing after said certain period of time.
 7. A device as defined in claim 1, wherein said detection probes and said calibration probes are fluorescent compounds, chemiluminescent compounds, phosphorescent compounds, or combinations thereof.
 8. A device as defined in claim 1, wherein said detection probes are fluorescent non-magnetic compounds.
 9. A device as defined in claim 1, wherein said calibration probes are fluorescent magnetic particles.
 10. A device as defined in claim 1, wherein said detection probes are capable of binding to the analyte.
 11. A device as defined in claim 1, further comprising non-fluorescent magnetic particles.
 12. A device as defined in claim 11, wherein said non-fluorescent magnetic particles are capable of binding to the analyte.
 13. A device as defined in claim 1, wherein said separated detection probes include complexes formed by said detection probes.
 14. A device as defined in claim 1, wherein said separated calibration probes include complexes formed by said calibration probes.
 15. A device as defined in claim 1, wherein the amount of the analyte within the test sample is proportional to the intensity of the detection signal generated by said separated detection probes at said detection zone divided by the intensity of the calibration signal generated by said separated calibration probes at said detection zone.
 16. A capillary flow assay device for detecting the presence or quantity of an analyte residing in a test sample, said device comprising: a reaction chamber, said reaction chamber being capable of containing a solution that comprises the test sample, detection probes capable of generating a detection signal, and magnetic calibration probes capable of generating a calibration signal; a capillary channel in communication with said reaction chamber, said fluidic capillary channel defining a detection zone; a barrier disposed between said reaction chamber and said capillary channel, said barrier being capable of holding said solution within said reaction chamber for a certain period of time; and a magnetic device positioned adjacent to said detection zone, said magnetic device being capable of separating said detection probes and said calibration probes from said solution; wherein the amount of the analyte within the test sample is proportional to the intensity of the detection signal generated by said separated detection probes at the detection zone calibrated by the intensity of the calibration signal generated by said separated calibration probes at the detection zone.
 17. A device as defined in claim 16, wherein said barrier is capable of being substantially dissolved by said solution.
 18. A device as defined in claim 17, wherein said barrier contains a material selected from the group consisting of carbohydrates, salts, and combinations thereof.
 19. A device as defined in claim 16, wherein said barrier is capable of physically rupturing after said certain period of time.
 20. A device as defined in claim 16, wherein said detection probes and said calibration probes are fluorescent compounds.
 21. A device as defined in claim 16, wherein said detection probes are fluorescent non-magnetic compounds.
 22. A device as defined in claim 16, wherein said calibration probes are fluorescent magnetic particles.
 23. A device as defined in claim 16, wherein said separated detection probes include complexes formed by said detection probes.
 24. A device as defined in claim 16, wherein said separated calibration probes include complexes formed by said calibration probes.
 25. A device as defined in claim 16, wherein the amount of the analyte within the test sample is proportional to the intensity of the detection signal generated by said separated detection probes at said detection zone divided by the intensity of the calibration signal generated by said separated calibration probes at said detection zone.
 26. A method for detecting the presence or quantity of an analyte residing in a test sample, said method comprising: i) providing a fluidics-based device, said device comprising: a) a reaction chamber containing detection probes capable of generating a detection signal and magnetic calibration probes capable of generating a calibration signal; b) a channel in fluid communication with said reaction chamber that defines a detection zone; and c) a magnetic device positioned adjacent to said detection zone; ii) applying a test sample containing the analyte to the reaction chamber to form a solution; iii) allowing said solution to flow from said reaction chamber to said detection zone of said channel; iv) separating said detection probes and said calibration probes from said solution at said detection zone using said magnetic device; v) exciting said separated detection probes and said separated calibration probes, wherein said excitation causes said separated detection probes to emit said detection signal and said separated calibration probes to emit said calibration signal; vi) measuring the intensity of the detection signal at a first emission wavelength and the intensity of the calibration signal at a second emission wavelength; and vii) comparing the intensity of the detection signal to the calibration signal, wherein the amount of the analyte within the test sample is proportional to the intensity of the detection signal calibrated by the intensity of the calibration signal.
 27. A method as defined in claim 26, further comprising holding the solution within said reaction chamber for a certain period of time with a barrier that is disposed between said reaction chamber and said channel.
 28. A method as defined in claim 26, wherein said detection and calibration probes are fluorescent.
 29. A method as defined in claim 26, wherein said detection and calibration probes are chemiluminescent.
 30. A method as defined in claim 26, wherein said detection and calibration probes are phosphorescent.
 31. A method as defined in claim 26, wherein said detection probes are non-magnetic.
 32. A method as defined in claim 26, wherein said separated detection probes include complexes formed by said detection probes.
 33. A method as defined in claim 29, wherein said complexes are formed with the analyte.
 34. A method as defined in claim 26, wherein said separated calibration probes include complexes formed by said calibration probes.
 35. A method as defined in claim 31, wherein said complexes are formed with the analyte.
 36. A method as defined in claim 26, wherein said first emission wavelength is different than said second emission wavelength.
 37. A method as defined in claim 26, further comprising generating a calibration curve by plotting the intensity of the detection signal calibrated by the intensity of the calibration signal for a plurality of predetermined analyte concentrations.
 38. A method as defined in claim 26, wherein said separated detection probes and said separated calibration probes are excited simultaneously.
 39. A method as defined in claim 26, wherein said separated detection probes and said separated calibration probes are excited separately.
 40. A method as defined in claim 26, wherein the intensity of the detection signal and the calibration signal are measured simultaneously.
 41. A method as defined in claim 26, wherein the intensity of the detection signal and the calibration signal are measured separately. 